JP6490519B2 - Ophthalmic microscope system - Google Patents

Description

  The present invention relates to an ophthalmic microscope system.

  In the field of ophthalmology, various microscopes are used for magnifying and observing the eye. Examples of such an ophthalmic microscope include a slit lamp microscope and a surgical microscope. Some ophthalmic microscopes include an image sensor for photographing an eye, and others include a binocular optical system that provides binocular parallax for stereoscopic observation.

  Ophthalmic microscopes may be used in combination with other ophthalmic devices. For example, as disclosed in Patent Document 1, a system in which an OCT (Optical Coherence Tomography) apparatus is combined with an ophthalmic microscope is known. The OCT apparatus is used for acquiring a cross-sectional image or a three-dimensional image of an eye, measuring a size (such as retinal thickness) of an eye tissue, acquiring functional information (such as blood flow information).

U.S. Pat. No. 8,049,873

  Standards that define requirements for the safety of light emission are applied to ophthalmic optical devices that emit light in or toward the eye. Such standards include standards related to protection from optical hazards. Regarding protection from optical hazards, for example, ISO (International Organization for Standardization) 150004-2: 2007 (Ophthalmic instruments: -2) It is stipulated in.

  However, in a system in which an OCT apparatus is combined with an ophthalmic microscope, for example, illumination light from an ophthalmic microscope and measurement light from an OCT apparatus may be simultaneously irradiated to an eye to acquire an OCT image during surgery. is there. When both eyes are irradiated to the subject eye so as to satisfy the above-mentioned standard, the amount of illumination light and measurement light emitted to the subject eye may be insufficient. When these light quantities are insufficient, the image quality of the observation image or OCT image based on the return light of the illumination light is degraded. On the other hand, if the amount of illumination light or measurement light is increased, the above-mentioned standard cannot be satisfied, and there is a possibility that the subject may be adversely affected. Thus, there is a trade-off relationship between the safety of the eye to be examined and the improvement of the image quality, and there is a problem that it is difficult to achieve both.

  The present invention has been made to solve such problems, and its purpose is to improve the image quality of observation images and OCT images while protecting against optical hazards even when the OCT apparatus is combined with an ophthalmic microscope. It is to provide a new technology that can be improved.

  The ophthalmic microscope system according to the embodiment includes an illumination system, a light receiving system, an interference optical system, a designation unit, and a control unit. The illumination system irradiates the eye to be examined with illumination light. The light receiving system guides the return light of the illumination light applied to the eye to be examined to the image sensor or the eyepiece lens system. The interference optical system divides the light from the OCT light source into measurement light and reference light, and detects interference light between the return light of the measurement light irradiated on the eye to be examined and the reference light. The designation unit is used for designating an operation mode. The control unit performs first light amount control for limiting the light amount of the measurement light so that the combined light amount of the illumination light and the measurement light is equal to or less than a predetermined value when the observation priority mode is designated by the designation unit. The control unit performs second light amount control for limiting the amount of illumination light so that the combined light amount is equal to or less than a predetermined value when the OCT priority mode is specified by the specifying unit.

  According to the embodiment, even when the OCT apparatus is combined with an ophthalmic microscope, it is possible to improve the image quality of an observation image and an OCT image while protecting from an optical hazard.

It is the schematic which shows an example of a structure of the ophthalmic microscope system which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope system which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope system which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope system which concerns on embodiment. It is the schematic which shows the effect | action of the ophthalmic microscope system which concerns on embodiment. It is a flowchart which shows the operation example of the ophthalmic microscope system which concerns on embodiment. It is the schematic which shows an example of a structure of the ophthalmic microscope system which concerns on a modification.

  An example of an embodiment of an ophthalmic microscope system according to the present invention will be described in detail with reference to the drawings. In addition, it is possible to use the description content of the literature referred in this specification, and arbitrary well-known techniques for the following embodiment.

  The ophthalmic microscope system is used for observing (capturing) an enlarged image of an eye to be examined in medical treatment or surgery in the ophthalmic field. The observation target part may be an arbitrary part of the patient's eye. For example, the anterior segment may be a cornea, a corner, a vitreous body, a crystalline lens, a ciliary body, or the like, and the retinal segment may be a retina or choroid. Or a vitreous body. Further, the observation target part may be a peripheral part of the eye such as a eyelid or an eye socket.

  The ophthalmic microscope system has a function as another ophthalmologic apparatus in addition to a function as a microscope for magnifying and observing an eye to be examined. In the following embodiments, an OCT function is provided as a function as another ophthalmologic apparatus. Other functions as an ophthalmologic apparatus may include laser treatment, axial length measurement, refractive power measurement, and higher-order aberration measurement in addition to the OCT function. Further, instead of the OCT function, laser treatment, axial length measurement, refractive power measurement, higher-order aberration measurement, and the like may be included. The other ophthalmologic apparatus may be provided with an arbitrary configuration capable of performing examination, measurement, and imaging of the eye to be examined by an optical method.

  Hereinafter, the return light of the illumination light applied to the eye to be examined is guided to the image sensor, and an image based on the output from the image sensor is displayed on the display unit provided in the eyepiece, thereby allowing the observer to view the image of the eye to be examined. A case where the embodiment is applied to an ophthalmic microscope system that presents However, it is also possible to apply the following embodiment to an ophthalmic microscope system that presents an image of the subject's eye to the observer by guiding the return light of the illumination light applied to the subject's eye to the eyepiece lens system.

[Constitution]
1 to 5 show a configuration example of an ophthalmic microscope system according to an embodiment. 1 to 3 and FIG. 5 show configuration examples of optical systems of an ophthalmic microscope system. FIG. 1 shows an optical system for observing the posterior eye part, and FIG. 2 shows an optical system for observing the anterior eye part. FIG. 4 shows the configuration of the processing system.

  The ophthalmic microscope system 1 includes an illumination system 10 (10L, 10R), a light receiving system 20 (20L, 20R), an eyepiece system 30 (30L, 30R), an irradiation system 40, and an OCT system 60. When observing the posterior eye portion (retinal or the like), the front lens 90 is disposed immediately before the eye E to be examined. A contact lens or the like can be used instead of the non-contact front lens 90 as shown in FIG. In addition, when observing the corner angle, a contact mirror (three-sided mirror or the like) can be used.

(Lighting system 10)
The illumination system 10 irradiates the eye E with illumination light. Although illustration is omitted, the illumination system 10 includes a light source that emits illumination light, a diaphragm that defines an illumination field according to a variable diaphragm value, a lens system, and the like. The illumination system 10 can change at least one of the amount and intensity of illumination light irradiated to the eye E under the control of the control unit 100 described later. The “intensity” of light is a light amount per unit time in a unit area, and the “light amount” is a physical quantity obtained by integrating the “intensity” over time. Therefore, in the following embodiments, “light quantity” and “intensity” are regarded as the same unless otherwise specified.

  For example, a light source that emits illumination light emits illumination light with a light amount corresponding to a control amount (voltage value, current value, etc.) specified by a control signal from the control unit 100. Thereby, the control part 100 can change the light quantity of illumination light by controlling with respect to a light source. In addition, the control unit 100 can acquire a control amount (voltage value, current value, etc.) set for the light source and detect the amount of illumination light corresponding to the acquired control amount. For example, the control unit 100 stores in advance a control table in which a control amount is associated with the amount of illumination light corresponding to the control amount. The control unit 100 specifies the amount of illumination light corresponding to the acquired control amount by referring to the control table. Alternatively, the illumination system 10 may include an illumination light amount detector that detects the amount of illumination light emitted by the light source. In this case, the control unit 100 can detect the light amount of the illumination light based on the detection result by the illumination light amount detection unit.

  In addition, by specifying an aperture value by a control signal from the control unit 100, it is possible to change the amount of illumination light irradiated to the eye E. Further, the illumination system 10 may be able to change the irradiation angle of the illumination light with respect to the eye E by changing the direction of the light source and the angle of a beam splitter 11L (11R) described later with respect to the optical axis of the light receiving system 20. . By changing the irradiation angle of the illumination light based on the control signal from the control unit 100, it is possible to change the amount of illumination light irradiated to the eye E.

  The illumination system 10 may include an ND (Neutral Density) filter that reduces the amount of illumination light. The ND filter is a neutral density filter that can be inserted into and removed from the optical path of the illumination light. In this case, the illumination system 10 includes a moving mechanism (not shown) for inserting an ND filter in the optical path of the illumination light and for retracting the ND filter from the optical path. The moving mechanism receives a control signal from the control unit 100, and inserts an ND filter into the optical path of the illumination light or retracts the ND filter from the optical path based on the control signal. Thereby, it is possible to change the light quantity of the illumination light irradiated to the eye E to be examined. The ND filter may be inserted / removed at an arbitrary position in the illumination optical path.

  The configuration of the illumination system 10 may be the same as that of a conventional ophthalmologic apparatus (for example, a slit lamp microscope, a fundus camera, a refractometer, or the like).

The illumination systems 10L and 10R of the present embodiment are configured coaxially with the light receiving systems 20L and 20R, respectively. Specifically, the left light receiving system 20L for acquiring an image presented to the left eye E ₀ L of the observer is obliquely provided with a beam splitter 11L made of, for example, a half mirror. The beam splitter 11L coaxially couples the optical path of the left illumination system 10L to the optical path of the left light receiving system 20L. The illumination light output from the left illumination system 10L is reflected by the beam splitter 11L and illuminates the eye E to be examined coaxially with the left light receiving system 20L. Similarly, the right light receiving system 20R for acquiring an image presented to the right eye E ₀ R of the observer is obliquely provided with a beam splitter 11R that couples the optical path of the right illumination system 10R to the optical path of the right light receiving system 20R. Has been. The beam splitter 11R coaxially couples the optical path of the right illumination system 10R to the optical path of the right light receiving system 20R. The illumination light output from the right illumination system 10R is reflected by the beam splitter 11R and illuminates the eye E to be examined coaxially with the right light reception system 20R.

  The position of the illumination light with respect to the optical axis of the light receiving system 20L (20R) can be changed. This configuration is realized, for example, by providing means for changing the irradiation position of the illumination light with respect to the beam splitter 11L (11R) as in the conventional microscope for ophthalmic surgery.

  In this example, the beam splitter 11L (11R) is arranged between the objective lens 21L (21R) and the eye E, but the position where the optical path of the illumination light is coupled to the light receiving system 20L (20R) is received. It can be at any position in the system 20L (20R).

(Light receiving system 20)
In the present embodiment, a pair of left and right light receiving systems 20L and 20R are provided. The left light receiving system 20L has a configuration for acquiring an image presented to the left eye E ₀ L of the observer, and the right light receiving system 20R is used to acquire an image presented to the right eye E ₀ R. Having a configuration. The left light receiving system 20L and the right light receiving system 20R have the same configuration. The left light receiving system 20L (right light receiving system 20R) includes an objective lens 21L (21R), an imaging lens 22L (22R), and an image sensor 23L (23R).

  A configuration in which the imaging lens 22L (22R) is not provided can also be applied. When the imaging lens 22L (22R) is provided as in the present embodiment, an afocal optical path (parallel optical path) is formed between the objective lens 21L (21R) and the imaging lens 22L (22R). it can. As a result, it becomes easy to arrange optical elements such as filters, and to arrange optical path coupling members to couple optical paths from other optical systems (that is, the degree of freedom and expandability of the optical configuration is improved). )

  Symbol AL1 indicates the optical axis (objective optical axis) of the objective lens 21L of the left light receiving system 20L, and symbol AR1 indicates the optical axis (objective optical axis) of the objective lens 21R of the right light receiving system 20R. The image sensor 23L (23R) is an area sensor such as a CCD image sensor or a CMOS image sensor.

  The above is the configuration of the light receiving system 20 when observing the posterior segment (fundus) of the eye E (FIG. 1). On the other hand, when observing the anterior segment, as shown in FIG. 2, the focus lens 24L (24R) and the wedge prism 25L (25R) are arranged at the position on the eye E side with respect to the objective lens 21L (21R). Is done. The focus lens 24L (24R) of this example is a concave lens, and acts to extend the focal length of the objective lens 21L (21R). The wedge prism 25L (25R) deflects the optical path (objective optical axis AL1 (AR1)) of the left light receiving system 20L (right light receiving system 20R) outward by a predetermined angle (indicated by symbols AL2 and AR2). Thus, the focus lens 24L and the wedge prism 25L are arranged in the left light receiving system 20L, and the focus lens 24R and the wedge prism 25R are arranged in the right light receiving system 20R. Accordingly, the focus position F1 for observing the posterior eye part is switched to the focus position F2 for observing the anterior eye part.

  A convex lens can be used as the focus lens. In this case, the focus lens is disposed in the optical path when observing the posterior eye part, and is retracted from the optical path when observing the anterior eye part. Instead of switching the focal length by inserting / retracting the focus lens, for example, by providing a focus lens that can move in the optical axis direction, the focal length can be changed continuously or stepwise.

  In the example shown in FIG. 2, the wedge prism 25L (25R) has a base direction outside (that is, a base-out arrangement), but a wedge prism having a base-in arrangement can be used. In this case, the wedge prism is disposed in the optical path when observing the posterior eye part, and is retracted from the optical path when observing the anterior eye part. Instead of switching the direction of the optical path by inserting / retracting the wedge prism, it is possible to change the direction of the optical path continuously or stepwise by providing a prism with a variable prism amount (and prism direction). is there.

(Eyepiece 30)
In the present embodiment, a pair of left and right eyepiece systems 30L and 30R are provided. Acquiring left eyepiece system 30L has a configuration to present an image of the eye E obtained by the left light receiving system 20L on the viewer's left eye E _{0 L,} right ocular system 30R is the right light receiving system 20R It has a configuration for presenting the image of the eye E to be examined to the right eye E ₀ R. The left eyepiece system 30L and the right eyepiece system 30R have the same configuration. The left eyepiece system 30L (right eyepiece system 30R) includes a display unit 31L (31R) and an eyepiece lens system 32L (32R).

  Display unit 31L (31R) is a flat panel display such as an LCD, for example. The size of the display surface of the display unit 31L (31R) is, for example, (diagonal length) 7 inches or less. The screen size of the display device provided in the pair of left and right eyepiece systems 30L and 30R depends on the eye width of the observer (distance between pupils, etc.), the size of the apparatus, the design of the apparatus (arrangement of optical systems and mechanisms, etc.), etc. Limited. That is, there is a trade-off between such constraints and the apparent field of view. From such a viewpoint, the maximum screen size of the display units 31L and 31R is considered to be about 7 inches. In addition, by devising the configuration of the eyepiece lens systems 32L and 32R and the arrangement of the mechanisms, the display units 31L and 31R having a screen size exceeding 7 inches can be applied, or the small-sized display units 31L and 31R can be applied. Can be applied.

It is possible to change the interval between the left eyepiece system 30L and the right eyepiece system 30R. Thereby, the interval between the left eyepiece system 30L and the right eyepiece system 30R can be adjusted according to the eye width of the observer. In addition, the relative orientation of the left eyepiece system 30L and the right eyepiece system 30R can be changed. That is, the angle formed by the optical axis of the left eyepiece system 30L and the optical axis of the right eyepiece system 30R can be changed. Thereby, the convergence of both eyes E ₀ L and E ₀ R can be induced, and stereoscopic viewing by the observer can be supported.

(Irradiation system 40)
The irradiation system 40 irradiates the eye E with light for realizing the function as the “other ophthalmologic apparatus” from a direction different from the objective optical axis (AL1 and AR1, and AL2 and AR2) of the light receiving system 20. To do. The irradiation system 40 of this example irradiates the eye E with light for OCT (measurement light).

  The irradiation system 40 includes an optical scanner 41, an imaging lens 42, a deflection mirror 43, and an OCT objective lens 44. Light from the OCT system 60 is guided to the optical scanner 41. The imaging lens 42 may be movable along the optical path of light from the OCT system 60 as a focus lens. In this case, a movement mechanism (not shown) receives a control signal from the control unit 100 described later, and moves the imaging lens 42 by a designated movement amount in a movement direction designated by the control signal.

  Light (measurement light) from the OCT system 60 is guided by the optical fiber 51 and emitted from the end face of the fiber. A collimating lens 52 is disposed at a position facing the fiber end face. The collimating lens 52 converts the measurement light emitted from the fiber end face into a parallel light beam. The measurement light converted into a parallel light beam by the collimator lens 52 is guided to the optical scanner 41. The collimating lens 52 may be movable along the optical path of the measurement light as a focus lens (or one of the lens groups constituting the focus lens). In this case, a moving mechanism (not shown) receives a control signal from the control unit 100 described later, and moves the collimator lens 52 by a specified moving amount in a moving direction specified by the control signal. Both the imaging lens 42 and the collimating lens 52 may be moved in conjunction or independently by a moving mechanism.

  The optical scanner 41 is a two-dimensional optical scanner, and includes an x scanner 41H that deflects light in the horizontal direction (x direction) and a y scanner 41V that deflects light in the vertical direction (y direction). Each of the x scanner 41H and the y scanner 41V may be an arbitrary type of optical scanner, and for example, a galvanometer mirror is used. The optical scanner 41 is disposed, for example, at the exit pupil position of the collimating lens 52 or a position in the vicinity thereof. Furthermore, the optical scanner 41 is disposed, for example, at the entrance pupil position of the imaging lens 42 or a position in the vicinity thereof.

  When a two-dimensional optical scanner is configured by combining two one-dimensional optical scanners as in this example, the two one-dimensional optical scanners are arranged apart from each other by a predetermined distance (for example, about 10 mm). Thereby, for example, any one-dimensional optical scanner can be arranged at the exit pupil position and / or the entrance pupil position.

  The imaging lens 42 temporarily forms an image of the parallel light flux (measurement light) that has passed through the optical scanner 41. The light that has passed through the imaging lens 42 is reflected by the deflection mirror 43 toward the OCT objective lens 44. The light passing through the OCT objective lens 44 is irradiated to the eye E.

  The position of the deflection mirror 43 is determined in advance so that the light guided by the irradiation system 40 is irradiated to the eye E from a direction different from the objective optical axis (AL1 and AR1, and AL2 and AR2) of the light receiving system 20. ing. In this example, the deflection mirror 43 is arranged at a position between the left light receiving system 20L and the right light receiving system 20R where the objective optical axes are arranged non-parallel.

(OCT system 60)
The OCT system 60 includes an interference optical system for performing OCT. An example of the configuration of the OCT system 60 is shown in FIG. The optical system shown in FIG. 3 is an example of a swept source OCT, which splits light from a wavelength scanning type (wavelength sweep type) light source into measurement light and reference light, and returns return light of measurement light from the eye E to be examined. Interference light is generated by interfering with the reference light passing through the reference light path, and this interference light is detected. The detection result (detection signal) of the interference light by the interference optical system is a signal indicating the spectrum of the interference light, and is sent to the control unit 100.

  The light source unit 61 includes a wavelength scanning type (wavelength sweeping type) light source capable of scanning (sweeping) the wavelength of emitted light in the same manner as a general swept source type OCT apparatus. The light source unit 61 temporally changes the output wavelength in the near-infrared wavelength band that cannot be visually recognized by the human eye.

  The OCT system 60 can change the amount of light L0 output from the light source unit 61 or measurement light LS described later. For example, the light source unit 61 outputs the light L0 with a light amount corresponding to a control amount (voltage value, current value, etc.) designated by a control signal from the control unit 100. Thereby, the control part 100 can change the light quantity of the light L0 by controlling with respect to the light source unit 61. FIG. Further, an attenuator may be provided between the light source unit 61 and a polarization controller 63 described later, and the light amount of the light L0 output from the light source unit 61 may be changed under the control of the control unit 100.

  An attenuator may be provided in the optical path of the measurement light LS guided to the eye E, and the light amount of the measurement light LS may be changed under the control of the control unit 100. In this case, an attenuator may be provided also in the optical path of the reference light LR, and the light amount of the reference light LR may be changed according to the change in the light amount of the measurement light LS under the control of the control unit 100. In the configuration shown in FIG. 3, since the return light of the measurement light LS returns along the same path as described later, the amount of the return light of the measurement light LS is changed by the attenuator. Therefore, when the change amount (attenuation amount) of the reference light LR is RA and the change amount (attenuation amount) of the measurement light LS is SA, the light amount of the reference light LR is changed so that RA> SA. May be.

  The light L0 output from the light source unit 61 is guided to the polarization controller 63 by the optical fiber 62 and its polarization state is adjusted. When an attenuator is provided between the light source unit 61 and the polarization controller 63, the light L0 is guided to the attenuator by an optical fiber, and the amount of light is adjusted. The light L0 whose light amount has been adjusted is guided to the polarization controller 63 by the optical fiber 62. The light L0 whose polarization state is adjusted by the polarization controller 63 is guided to the fiber coupler 65 by the optical fiber 64 and is divided into the measurement light LS and the reference light LR.

  The reference light LR is guided to the collimator 67 by the optical fiber 66A, converted into a parallel light beam, and guided to the corner cube 70 via the optical path length correction member 68 and the dispersion compensation member 69. The optical path length correction member 68 functions as a delay unit for matching the optical path length (optical distance) of the reference light LR with the optical path length of the measurement light LS. The dispersion compensation member 69 acts as a dispersion compensation means for matching the dispersion characteristics between the reference light LR and the measurement light LS.

  The corner cube 70 folds the traveling direction of the reference light LR in the reverse direction. The corner cube 70 is movable in a direction along the incident optical path and the outgoing optical path of the reference light LR, thereby changing the length of the optical path of the reference light LR. Note that any one of a means for changing the length of the optical path of the measurement light LS and a means for changing the length of the optical path of the reference light LR may be provided.

  The reference light LR that has passed through the corner cube 70 passes through the dispersion compensation member 69 and the optical path length correction member 68, is converted from a parallel light beam into a focused light beam by the collimator 71, enters the optical fiber 72, and is guided to the polarization controller 73. Accordingly, the polarization state of the reference light LR is adjusted. Further, the reference light LR is guided to the attenuator 75 by the optical fiber 74, and the light amount is adjusted under the control of the control unit 100. The reference light LR whose light amount has been adjusted is guided to the fiber coupler 77 by the optical fiber 76.

  On the other hand, the measurement light LS generated by the fiber coupler 65 is guided by the optical fiber 51 and emitted from the end face of the fiber, and is converted into a parallel light beam by the collimator lens 52. The measurement light LS converted into a parallel light beam is irradiated to the eye E through the optical scanner 41, the imaging lens 42, the deflection mirror 43, and the OCT objective lens 44. The measurement light LS is reflected and scattered at various depth positions of the eye E. The return light of the measurement light LS from the eye E includes reflected light and backscattered light, travels in the same direction as the forward path in the reverse direction, is guided to the fiber coupler 65, and passes through the optical fiber 66B to the fiber coupler 77. To reach.

  The fiber coupler 77 combines (interferences) the measurement light LS incident through the optical fiber 66B and the reference light LR incident through the optical fiber 76 to generate interference light. The fiber coupler 77 generates a pair of interference light LC by dividing the interference light at a predetermined branching ratio (for example, 1: 1). The pair of interference lights LC emitted from the fiber coupler 77 are guided to the detector 79 by optical fibers 78A and 78B, respectively.

  The detector 79 is, for example, a balanced photodiode that includes a pair of photodetectors that respectively detect a pair of interference lights LC and outputs a difference between detection results obtained by these. The detector 79 sends the detection result (detection signal) to the control unit 100.

  In this embodiment, the amount of light of the illumination light and the measurement light LS is limited according to the operation mode designated in advance, so that the combined light amount of the illumination light and the measurement light LS is less than a predetermined value. The optometry E is irradiated with illumination light and measurement light LS. The combined light amount is the sum of the light amount of illumination light and the light amount of the measurement light LS that are simultaneously irradiated to the eye E. The predetermined value is determined in advance based on, for example, a value defined in a standard related to protection from optical hazard. The OCT system 60 may include a light amount detection unit 80 that detects the light amount of the light L0 or the measurement light LS from the light source unit 61 in order to monitor the combined light amount. By detecting the light amount of the light L0 or the measurement light LS by the light amount detection unit 80, the control unit 100 can specify the limit amount of the light amount of the measurement light LS. Moreover, the control part 100 can specify the light quantity of illumination light by acquiring the control amount etc. which were set with respect to the light source of the illumination system 10, for example. Accordingly, the control unit 100 can limit the light amount of the illumination light or the measurement light LS so that the combined light amount is equal to or less than a predetermined value while monitoring the light amounts of the illumination light and the measurement light LS.

  In this example, swept source OCT is applied, but other types of OCT, such as spectral domain OCT, can be applied.

(Control unit 100)
The control part 100 performs control of each part of the ophthalmic microscope system 1 (see FIG. 4). Examples of the control of the illumination system 10 include the following: turning on / off the light source, adjusting the light amount, detecting the light amount; changing the aperture value of the aperture 10a; insertion / removal control of the ND filter 10b; Adjust the slit width. The light amount adjustment is a light amount adjustment of illumination light performed by setting a control amount for the light source. The light amount detection is a light amount detection of illumination light performed by acquiring a control amount set for the light source. Control of the image sensor 23 includes exposure adjustment, gain adjustment, and shooting rate adjustment.

  The control unit 100 displays various information on the display unit 31. For example, the control unit 100 causes the display unit 31L to display an image acquired by the image sensor 23L (or an image obtained by processing the image) and displays an image acquired by the image sensor 23R (or processes it). The image obtained in this manner is displayed on the display unit 31R.

  As control of the optical scanner 41, for example, the measurement light LS is sequentially deflected so that the measurement light LS is irradiated to a plurality of positions according to a preset OCT scan pattern.

  Control targets included in the OCT system 60 include a light source unit 61, an attenuator 62a, a polarization controller 63, a corner cube 70, a polarization controller 73, an attenuator 75, a detector 79, a light amount detector 80, and the like.

  As described above, the attenuator 62a is provided between the light source unit 61 and the polarization controller 63, and adjusts the amount of light L0 from the light source unit 61. As control of the attenuator 62a, the light amount of the light L0 is attenuated by the attenuation amount specified by the control signal.

  The light amount detection unit 80 detects the light amount of the light L0 or the measurement light LS from the light source unit 61. For example, an optical path separation member is disposed in the optical path of the light L0 or the optical path of the measurement light LS. The optical path separating member separates the monitoring optical path from the optical path of the light L0 or the optical path of the measurement light LS. The light quantity detection unit 80 is disposed in the monitoring optical path separated by the optical path separation member. Such a light quantity detection unit 80 includes, for example, a fiber coupler and a detector, similarly to the configuration shown in FIG. A detection signal from the light amount detection unit 80 is sent to the control unit 100.

  Furthermore, the control unit 100 controls various mechanisms. As such a mechanism, a stereo angle changing unit 20A, a focusing unit 24A, an optical path deflecting unit 25A, an interval changing unit 30A, and an orientation changing unit 30B are provided.

  The stereo angle changing unit 20A relatively rotates and moves the left light receiving system 20L and the right light receiving system 20R. That is, the stereo angle changing unit 20A relatively moves the left light receiving system 20L and the right light receiving system 20R so as to change the angle formed by the objective optical axes (for example, AL1 and AR1). This relative movement is, for example, to move the left light receiving system 20L and the right light receiving system 20R by the same angle in opposite rotational directions. In this movement mode, the direction of the angle bisector formed by the objective optical axes (for example, AL1 and AR1) is constant. On the other hand, it is also possible to perform the relative movement so that the direction of the bisector changes.

  An example of a state in which the stereo angle is enlarged from the state shown in FIG. 2 is shown in FIG. The stereo angle may be defined as an angle formed by the objective optical axis AL1 of the left light receiving system 20L and the objective optical axis AR1 of the right light receiving system 20R, or the objective optical axis AL2 of the left light receiving system 20L and the right light receiving system. It may be defined as an angle formed by the 20R objective optical axis AR2. Even if the stereo angle is changed by the stereo angle changing unit 20A, the relative positions (intervals and relative orientations) of the left and right eyepiece systems 30L and 30R do not change. Further, the focal position is adjusted by adjusting the distance between the left and right light receiving systems 20L and 20R with respect to the eye E or changing the focal length of the left and right light receiving systems 20L and 20R in response to the change in the stereo angle. Control can be performed so as not to move.

  The focusing unit 24A inserts / withdraws the left and right focus lenses 24L and 24R with respect to the optical path. The focusing unit 24A may be configured to simultaneously insert / retract the left and right focus lenses 24L and 24R. In another example, the focusing unit 24A may be configured to change the focal position by moving the left and right focus lenses 24L and 24R (simultaneously) in the optical axis direction. Alternatively, the focusing unit 24A may be configured to change the focal length by changing (simultaneously) the refractive powers of the left and right focus lenses 24L and 24R.

  The optical path deflecting unit 25A inserts / withdraws the left and right wedge prisms 25L and 25R with respect to the optical path. The optical path deflecting unit 25A may be configured to simultaneously insert / retract the left and right wedge prisms 25L and 25R. In another example, the optical path deflecting unit 25A changes the direction of the optical paths of the left and right light receiving systems 20L and 20R by changing the prism amounts (and prism directions) of the left and right wedge prisms 25L and 25R (simultaneously). May be configured.

  The interval changing unit 30A changes the interval between the left and right eyepiece systems 30L and 30R. The interval changing unit 30A may be configured to relatively move the left and right eyepiece systems 30L and 30R without changing the relative directions of the optical axes of each other.

  The orientation changing unit 30B changes the relative orientation of the left and right eyepiece systems 30L and 30R. The direction changing unit 30B relatively moves the left eyepiece system 30L and the right eyepiece system 30R so as to change the angle formed by the optical axes of each other. This relative movement is, for example, to move the left eyepiece system 30L and the right eyepiece system 30R by the same angle in opposite rotation directions. In this movement mode, the direction of the bisector of the angle formed by the optical axes of each other is constant. On the other hand, it is also possible to perform the relative movement so that the direction of the bisector changes.

  As described above, the control unit 100 can specify the amount of illumination light and the amount of measurement light LS. The control unit 100 restricts the light amount of the measurement light LS based on the specified light amount of the illumination light and the light amount of the measurement light LS so that the combined light amount of the illumination light and the measurement light LS is equal to or less than a predetermined value. One light quantity control can be executed. The control unit 100 can limit the amount of the measurement light LS by controlling at least one of the light source unit 61 and the attenuator 62a. Further, the control unit 100 limits the light amount of the illumination light based on the specified light amount of the illumination light and the light amount of the measurement light LS so that the combined light amount of the illumination light and the measurement light LS is equal to or less than a predetermined value. It is possible to execute the second light quantity control. The control unit 100 can limit the amount of illumination light by controlling at least one of the light source of the illumination system 10, the irradiation angle of illumination light to the eye E, the aperture value of the aperture 10a, and the ND filter 10b.

  The control unit 100 executes the first light amount control or the second light amount control according to the operation mode. In this embodiment, the operation modes include an observation priority mode (illumination light priority mode) and an OCT priority mode (OCT light priority mode). In the observation priority mode, by restricting the light amount of the measurement light LS so that the combined light amount is equal to or less than a predetermined value, the illumination light and the measurement light LS are simultaneously irradiated onto the eye E while securing the light amount of the illumination light. Is the operation mode. In the observation priority mode, it is possible to improve the image quality of the observation image based on the return light of the illumination light rather than the image quality of the OCT image while protecting from the light hazard. In the OCT priority mode, the illumination light and the measurement light LS are simultaneously irradiated to the eye E while securing the light quantity of the measurement light LS by limiting the light quantity of the illumination light so that the combined light quantity is less than a predetermined value. Is the operation mode. In the OCT priority mode, it is possible to improve the image quality of the OCT image over the image quality of the observation image while protecting from light hazard. At this time, the control unit 100 can perform at least one of the first light amount control and the second light amount control based on the detection result by the light amount detection unit 80.

  In addition, the control part 100 may restrict | limit the light quantity of the measurement light LS or illumination light by reducing the irradiation time of the measurement light LS or illumination light with respect to the eye E to be examined. Thereby, it becomes possible to restrict the light quantity of the measurement light LS or the illumination light without restricting the intensity of the measurement light LS or the illumination light, and the first light quantity control or the second light quantity control can be simplified. .

  Further, the control unit 100 may control the detector 79 so that the detection sensitivity of the interference light LC is increased in the observation priority mode. The control of the detector 79 includes increasing the gain for the detection signal obtained by the detector 79, increasing the detection signal acquisition timing, and the like. Thereby, even when the light amount of the measurement light LS is limited in the observation priority mode, it is possible to suppress the deterioration of the image quality of the OCT image.

(Data processing unit 200)
The data processing unit 200 executes various types of data processing. This data processing includes processing for forming an image, processing for processing an image, and the like. In addition, the data processing unit 200 may be capable of executing processing relating to analysis of images, examination results, and measurement results, and information relating to the subject (such as electronic medical record information). The data processing unit 200 includes a scaling processing unit 210 and an OCT image forming unit 220.

The scaling processing unit 210 enlarges the image acquired by the image sensor 23. This process is a so-called digital zoom process, and includes a process of cutting out a part of an image acquired by the image sensor 23 and a process of creating an enlarged image of the part. The image clipping range is set by the observer or by the control unit 100. The scaling processing unit 210 performs the same processing on the image (left image) acquired by the imaging device 23L of the left light receiving system 20L and the image (right image) acquired by the imaging device 23R of the right light receiving system 20R. Apply. Thereby, images of the same magnification are presented to the left eye E ₀ L and the right eye E ₀ R of the observer.

  In addition to or instead of such a digital zoom function, a so-called optical zoom function can be provided. The optical zoom function is realized by providing a variable magnification lens (variable lens system) in each of the left and right light receiving systems 20L and 20R. As a specific example, there is a configuration in which the zoom lens is (selectively) inserted / retracted with respect to the optical path, or a configuration in which the zoom lens is moved in the optical axis direction. Control related to the optical zoom function is executed by the control unit 100.

  The OCT image forming unit 220 forms an image of the eye E based on the detection result of the interference light LC obtained by the detector 79 of the OCT system 60. The control unit 100 sends detection signals sequentially output from the detector 79 to the OCT image forming unit 220. The OCT image forming unit 220 performs, for example, Fourier transform or the like on the spectrum distribution based on the detection result obtained by the detector 79 for each series of wavelength scans (for each A line), thereby reflecting the reflection intensity profile in each A line. Form. Further, the OCT image forming unit 220 forms image data by imaging each A-line profile. Thereby, a B-scan image (cross-sectional image) and volume data (three-dimensional image data) are obtained.

  The data processing unit 200 may have a function of analyzing the image (OCT image) formed by the OCT image forming unit 220. This analysis function includes retinal thickness analysis and comparative analysis with normal eyes. Such an analysis function is executed using a known application. Further, the data processing unit 200 may have a function of analyzing an image acquired by the light receiving system 20. The data processing unit 200 may include an analysis function that combines analysis of an image acquired by the light receiving system 20 and analysis of an OCT image.

(User interface 300)
The user interface (UI) 300 has a function for exchanging information between an observer or the like and the ophthalmic microscope system 1. The user interface 300 includes a display device and an operation device (input device). In this embodiment, the user interface 300 is used, for example, for designating an operation mode of the ophthalmic microscope system 1 or instructing execution of OCT measurement. The display device may include the display unit 31 and may include other display devices. The operation device includes various hardware keys and / or software keys. It is possible to integrally configure at least a part of the operation device and at least a part of the display device. A touch panel display is an example.

(Communication unit 400)
The communication unit 400 performs a process for transmitting information to another apparatus and a process for receiving information transmitted from the other apparatus. The communication unit 400 may include a communication device that conforms to a predetermined network (LAN, Internet, etc.). For example, the communication unit 400 acquires information from an electronic medical record database or a medical image database via a LAN provided in a medical institution. In the case where an external monitor is provided, the communication unit 400 converts an image acquired by the ophthalmic microscope system 1 (an image acquired by the light receiving system 20, an OCT image, etc.) to the external monitor substantially in real time. Can be sent.

  The OCT system 60 is an example of an “interference optical system” according to the embodiment. The light source unit 61 is an example of an “OCT light source” according to the embodiment. The user interface 300 is an example of a “designating unit” according to the embodiment. The ND filter 10b is an example of a “filter” according to the embodiment.

[Operation example]
FIG. 6 shows a flowchart of an operation example of the ophthalmic microscope system 1 according to the embodiment. FIG. 6 shows an operation example when the operation mode of the ophthalmic microscope system 1 is switched.

  The operation mode of the ophthalmic microscope system 1 may be automatically specified by the control unit 100 or manually specified using the user interface 300. The control unit 100 can switch the operation mode of the ophthalmic microscope system 1 to the designated operation mode at an arbitrary timing.

(S1)
When the power of the ophthalmic microscope system 1 is turned on, the control unit 100 sets the operation mode of the ophthalmic microscope system 1 to the observation priority mode.

(S2)
The control unit 100 determines whether or not to perform OCT measurement. For example, whether or not to perform OCT measurement is instructed by the user using the user interface 300. The control unit 100 can determine whether or not to perform OCT measurement based on the user's operation content on the user interface 300. When it is determined to perform the OCT measurement (S2: Y), the operation of the ophthalmic microscope system 1 proceeds to S3. When it is not determined to execute the OCT measurement (S2: N), the operation of the ophthalmic microscope system 1 proceeds to S4.

(S3)
When it is determined that the OCT measurement is to be executed (S2: Y), the control unit 100 switches the operation mode of the ophthalmic microscope system 1 from the observation priority mode to the OCT priority mode. In the OCT priority mode, as described above, based on the light quantity of the specified illumination light and the light quantity of the measurement light LS, the light quantity of the measurement light LS is ensured to be a composite light quantity equal to or less than a predetermined value. The amount of light is limited. The operation of the ophthalmic microscope system 1 proceeds to S8.

(S4)
When it is not determined to execute the OCT measurement (S2: N), the control unit 100 determines whether or not to switch the operation mode. For example, whether to switch the operation mode is instructed by the user using the user interface 300. The control unit 100 can determine whether or not to switch the operation mode based on the user's operation content on the user interface 300. When it is determined that the operation mode is to be switched (S4: Y), the operation of the ophthalmic microscope system 1 proceeds to S5. When it is not determined to switch the operation mode (S4: N), the operation of the ophthalmic microscope system 1 proceeds to S8.

(S5)
When it is determined that the operation mode is to be switched (S4: Y), the control unit 100 determines whether to switch to the observation priority mode. For example, the control unit 100 can determine whether to switch to the observation priority mode based on the user's operation content on the user interface 300. When it is determined to switch to the observation priority mode (S5: Y), the operation of the ophthalmic microscope system 1 proceeds to S6. When it is not determined to switch to the observation priority mode (S5: N), the operation of the ophthalmic microscope system 1 proceeds to S7.

(S6)
When it is determined to switch to the observation priority mode (S5: Y), the control unit 100 sets the operation mode after switching to the observation priority mode. When the operation mode before switching is the observation priority mode, the control unit 100 continues the operation mode as the observation priority mode. When the operation mode before switching is the OCT priority mode, the control unit 100 switches the operation mode from the OCT priority mode to the observation priority mode. In the observation priority mode, as described above, based on the light quantity of the specified illumination light and the light quantity of the measurement light LS, the light quantity of the measurement light LS is secured while securing the light quantity of the illumination light so that the combined light quantity is equal to or less than a predetermined value. The amount of light is limited. As a result, even when an OCT image is acquired during surgery, it is possible to acquire a high-quality observation image while protecting from light hazard. The operation of the ophthalmic microscope system 1 proceeds to S8.

(S7)
When it is not determined to switch to the observation priority mode (S5: N), the control unit 100 sets the operation mode after switching to the OCT priority mode. When the operation mode before switching is the OCT priority mode, the control unit 100 continues the operation mode as the OCT priority mode. When the operation mode before switching is the observation priority mode, the control unit 100 switches the operation mode from the observation priority mode to the OCT priority mode. Thereby, even when an OCT image is acquired during surgery, it is possible to temporarily acquire a high-quality OCT image while protecting from light hazard. The operation of the ophthalmic microscope system 1 proceeds to S8.

(S8)
The control unit 100 determines whether or not to end the operation of the ophthalmic microscope system 1. For example, the end of the operation is instructed by the user using the user interface 300. The control unit 100 can determine whether or not to end the operation based on the content of the user operation on the user interface 300. When it is not determined to end the operation (S8: N), the operation of the ophthalmic microscope system 1 proceeds to S4. When it is determined that the operation is to be ended (S8: Y), the operation of the ophthalmic microscope system 1 is ended (END).

[effect]
The effect of the ophthalmic microscope system of the embodiment will be described.

  An ophthalmic microscope system (ophthalmic microscope system 1) according to the embodiment includes an illumination system (illumination system 10), a light receiving system (light receiving system 20), an interference optical system (OCT system 60), and a designation unit (user interface). 300) and a control unit (control unit 100). The illumination system irradiates the eye to be examined (eye E to be examined) with illumination light. The light receiving system guides the return light of the illumination light applied to the eye to be examined to the imaging device (imaging device 23) or the eyepiece system. The interference optical system divides light (light L0) from the OCT light source (light source unit 61) into measurement light (measurement light LS) and reference light (reference light LR), and returns the measurement light irradiated to the eye to be examined. Interference light (interference light LC) between the light and the reference light is detected. The designation unit is used for designating an operation mode. The control unit performs first light amount control for limiting the light amount of the measurement light so that the combined light amount of the illumination light and the measurement light is equal to or less than a predetermined value when the observation priority mode is designated by the designation unit. The control unit performs second light amount control for limiting the amount of illumination light so that the combined light amount is equal to or less than a predetermined value when the OCT priority mode is specified by the specifying unit.

  According to such a configuration, the light amount of the illumination light or the measurement light is limited according to the operation mode so that the combined light amount of the illumination light and the measurement light becomes a predetermined value. It is possible to achieve both improvement in image quality according to the operation mode. Thereby, even when the interference optical system is combined with the light receiving system, the image quality corresponding to the operation mode can be improved while protecting from the light hazard.

  The ophthalmic microscope system according to the embodiment may include a light amount detection unit (light amount detection unit 80). The light quantity detection unit detects the light quantity of the light from the OCT light source or the measurement light. The control unit performs at least one of the first light amount control and the second light amount control based on the detection result by the light amount detection unit.

  According to such a configuration, based on the detection result of the light amount of the OCT light source or the measurement light, the light amount of the illumination light or the measurement light LS is limited so that the combined light amount is equal to or less than a predetermined value. Is possible.

  The ophthalmic microscope system according to the embodiment may include an attenuator (attenuator 62a). The attenuator adjusts the amount of light from the OCT light source or measurement light. The control unit limits the amount of measurement light by controlling at least one of the OCT light source and the attenuator.

  According to such a configuration, it is possible to easily and accurately limit the amount of measurement light in the observation priority mode.

  In the ophthalmic microscope system according to the embodiment, the illumination system may be able to change the irradiation angle of the illumination light with respect to the eye to be examined. The illumination system includes a stop (stop 10a) and a filter (ND filter 10b). The aperture value is variable. The filter can be inserted into and removed from the optical path of the illumination light. The control unit limits the amount of illumination light by controlling at least one of the light source, illumination angle, aperture value, and filter of the illumination system.

  According to such a configuration, it is possible to easily and accurately limit the amount of illumination light in the OCT priority mode.

  In the ophthalmic microscope system according to the embodiment, the control unit may limit the amount of the measurement light or the illumination light by reducing the irradiation time of the measurement light or the illumination light on the eye to be examined.

  According to such a configuration, it becomes possible to limit the light amount of the measurement light or the illumination light without limiting the intensity of the measurement light or the illumination light, thereby simplifying the first light amount control or the second light amount control. Will be able to.

  In the ophthalmic microscope system according to the embodiment, the interference optical system may include a detector (detector 79). The detector detects the interference light. The control unit controls the detector so that the detection sensitivity of the interference light increases when the observation priority mode is designated.

  According to such a configuration, even when the amount of measurement light is limited in the observation priority mode, it is possible to suppress deterioration in image quality based on the detection result of interference light.

[Modification]
The above embodiments are merely examples for carrying out the present invention. A person who intends to implement the present invention can make arbitrary modifications, omissions, additions, substitutions and the like within the scope of the present invention. Hereinafter, the drawings in the above embodiments will be referred to as appropriate.

(Modification 1)
In the above embodiment, the focus lenses 24L and 24R and the wedge prisms 25L and 25R are retracted from the optical path during fundus observation, and are inserted into the optical path during anterior segment observation. Such an operation can be automated. In the embodiment, an auxiliary optical member for changing the observation site of the eye to be examined is used. For example, the front lens 90 is disposed in the optical path during fundus observation and is retracted from the optical path during anterior eye observation.

  The ophthalmic microscope system according to the present modification changes the states of the focus lenses 24L and 24R according to the state of the auxiliary optical member (that is, selection of the observation site). That is, the control unit 100 controls the second mechanism for linking the focus lenses 24L and 24R according to the change of the observation site by the auxiliary optical member. Similarly, the control unit 100 controls the third mechanism for operating the wedge prisms 25L and 25R in association with changes in the observation site by the auxiliary optical member.

  A specific example will be described. When the front lens 90 is retracted from the optical path, the control unit 100 controls the focusing unit 24A and the optical path deflecting unit 25A so that the focus lenses 24L and 24R and the wedge prisms 25L and 25R are inserted into the optical path. . Conversely, the control unit 100 controls the focusing unit 24A and the optical path deflecting unit 25A so as to retract from the focus lenses 24L and 24R and the wedge prisms 25L and 25R in response to the insertion of the front lens 90 in the optical path. To do.

  The ophthalmic microscope system according to this modification may include a configuration for generating information indicating the state of the auxiliary optical member (for example, whether or not the front lens 90 is inserted in the optical path). For example, the arrangement state of the arm that holds the front lens 90 can be detected using a sensor such as a microswitch. Alternatively, in the configuration in which the insertion / retraction of the front lens 90 is performed based on a signal from the control unit 100, the current state of the front lens 90 can be recognized by referring to the control history.

  As another example, based on the image acquired by the image sensor 23L and / or 23R and the current state of the focus lenses 24L and 24R and the wedge prisms 25L and 25R, is the front lens 90 disposed in the optical path? It can be determined whether or not. For example, the data processing unit 200 analyzes an image acquired in a state where the focus lens 24L and the like are arranged on the optical path, thereby obtaining an amount indicating the blurred state of the image. When the amount of blur is equal to or greater than the threshold value, it is determined that the front lens 90 is disposed in the optical path. Conversely, if the amount of blur is less than the threshold value, it is determined that the front lens 90 is retracted from the optical path. In the case of analyzing an image acquired in a state where the focus lens 24L is retracted from the optical path, the state of the front lens 90 can be determined in the same manner.

  According to this modification, the state of the lens for changing the focal position (focus lenses 24L and 24R) and the state of the deflection member (wedge prisms 25L and 25R) for deflecting the optical path are used for switching the observation site. It can be changed automatically. Therefore, the operability can be further improved.

(Modification 2)
The illumination systems (10L and 10R) of the above embodiment are arranged coaxially with the pair of light receiving systems (20L and 20R). In this modification, a configuration in which an illumination system is arranged non-coaxially with respect to a pair of light receiving systems, that is, a configuration in which illumination light can be irradiated from a direction different from the objective optical axis of the pair of light receiving systems will be described. A configuration example of the optical system of this modification is shown in FIG. The illumination system 10 </ b> S of the ophthalmic microscope system 1 </ b> A can irradiate, for example, slit light to the eye as an attached illumination system. A typical example of such an ophthalmic microscope is a slit lamp microscope. In the present modification, the relative positions of the illumination system 10S and the light receiving systems 20L and 20R can be changed like a slit lamp microscope. That is, the illumination system 10S and the light receiving systems 20L and 20R are configured to be rotatable around the same axis. Thereby, it is possible to observe the cross section of the cornea etc. illuminated with the slit light from an oblique direction.

  The slit light by the illumination system 10S corresponds to part or all of the illumination light according to the above embodiment. That is, the slit light from the illumination system 10S and the illumination light according to the above embodiment can be applied to the above embodiment as illumination light according to this modification. Therefore, the control unit of the ophthalmic microscope system 1A performs the first light amount control for limiting the light amount of the measurement light LS so that the combined light amount of the slit light, the illumination light, and the measurement light LS by the illumination system 10S is equal to or less than a predetermined value. It is possible to execute. In addition, the control unit executes the second light amount control for limiting the light amount of the slit light or the illumination light so that the combined light amount of the slit light, the illumination light, and the measurement light LS by the illumination system 10S is equal to or less than a predetermined value. Is possible. The control unit can limit the light amount of the slit light by controlling the light source of the illumination system 10S, the diaphragm, the filter, and the like included in the illumination system 10S.

  The ophthalmic microscope system may include one or both of a coaxial illumination system as in the above embodiment and a non-coaxial illumination system as in this modification. When both illumination systems are provided, the illumination system to be used can be switched in accordance with, for example, switching of the observation site.

  In the embodiment or the modification described above, the case where the light amount of the illumination light or the measurement light is limited so that the combined light amount of the illumination light and the measurement light is equal to or less than the predetermined value has been described, but the combined light amount is less than the predetermined value. In addition, the amount of illumination light or measurement light may be limited.

  In the embodiment or the modification described above, the limitation of the light amount of the measurement light in the first light amount control may include setting the light amount of the measurement light to zero (stopping the measurement light irradiation). Further, the limitation of the amount of illumination light in the second light amount control may include setting the amount of illumination light to be substantially zero (the amount of illumination light> 0).

  In the above embodiment or modification, the ND filter has been described as an example of a filter that can be inserted into and removed from the optical path of the illumination light. However, the filter may be a filter other than the ND filter.

DESCRIPTION OF SYMBOLS 1 Ophthalmic microscope system 10 Illumination system 20 Light receiving system 21L Objective lens 21R Objective lens 23, 23L, 23R Imaging element 30, 30L, 30R Eyepiece system 40 Irradiation system 43 Deflection mirror 44 OCT objective lens 60 OCT system 80 Light quantity detection part 100 Control 300 User interface

Claims (6)

An illumination system that illuminates the eye to be examined; and
A light receiving system that guides the return light of the illumination light applied to the eye to be imaged to an image sensor or an eyepiece system;
An interference optical system that divides light from the OCT light source into measurement light and reference light, and detects interference light between the return light of the measurement light irradiated on the eye to be examined and the reference light;
A specification part for specifying an operation mode;
When the observation priority mode is designated by the designation unit, a first light amount control is performed to limit a light amount of the measurement light so that a combined light amount of the illumination light and the measurement light is not more than a predetermined value. A control unit that performs second light amount control for limiting the amount of illumination light so that the combined light amount is equal to or less than the predetermined value when the OCT priority mode is designated;
Including ophthalmic microscope system. A light amount detection unit for detecting the light amount of the OCT light source or the measurement light,
The ophthalmic microscope system according to claim 1, wherein the control unit performs at least one of the first light amount control and the second light amount control based on a detection result by the light amount detection unit. An attenuator for adjusting the amount of light from the OCT light source or the measurement light;
The ophthalmic microscope system according to claim 1, wherein the control unit limits the amount of the measurement light by controlling at least one of the OCT light source and the attenuator. The illumination system can change an irradiation angle of the illumination light with respect to the eye to be examined,
The illumination system is
An aperture with variable aperture value,
A filter that can be inserted into and removed from the optical path of the illumination light;
Including
The said control part restrict | limits the light quantity of the said illumination light by controlling at least 1 of the light source of the said illumination system, the said irradiation angle, the said aperture value, and the said filter. The ophthalmic microscope system according to any one of the above. The said control part restrict | limits the light quantity of the said measurement light or the said illumination light by reducing the irradiation time of the said measurement light or the said illumination light with respect to the said eye to be examined. The ophthalmic microscope system according to claim 1. The interference optical system includes a detector that detects the interference light,
The said control part controls the said detector so that the detection sensitivity of the said interference light rises when the said observation priority mode is designated. The Claim 1 characterized by the above-mentioned. Ophthalmic microscope system.

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